EP0451233B1 - Dispositif implantable d'evaluation du taux de glucose - Google Patents

Dispositif implantable d'evaluation du taux de glucose Download PDF

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Publication number
EP0451233B1
EP0451233B1 EP90914732A EP90914732A EP0451233B1 EP 0451233 B1 EP0451233 B1 EP 0451233B1 EP 90914732 A EP90914732 A EP 90914732A EP 90914732 A EP90914732 A EP 90914732A EP 0451233 B1 EP0451233 B1 EP 0451233B1
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EP
European Patent Office
Prior art keywords
glucose
membrane
pressure
pressure sensor
measured
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Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
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EP90914732A
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German (de)
English (en)
French (fr)
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EP0451233A1 (fr
Inventor
Frédéric Neftel
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NEFTEL, FREDERIC
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Neftel Frederic
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02—Details of sensors specially adapted for in-vivo measurements
    • A61B2562/028—Microscale sensors, e.g. electromechanical sensors [MEMS]

Definitions

  • the present invention relates to the field of medical devices and, more particularly, to an implantable device allowing an accurate and simple evaluation of an individual's blood glucose level.
  • the object of the invention is to allow a precise evaluation of the blood glucose level of an individual, by a non-aggressive method and through a device of very small size which is implanted, for example, in subcutaneous territory.
  • the principle consists in precisely measuring, in an interstitial territory, the absolute value - or the variations - of the osmotic pressure due to molecules having a spatial bulk equivalent to that of glucose using a very small footprint implanted device. Such a measurement can be carried out in any territory or compartment in glucose balance with the vascular compartment. From the measured value, the osmotic pressure due to glucose is deduced, and therefore the circulating glucose level.
  • a pressure sensor according to such techniques could be advantageously used given its very small final size (a few mm2 over less than a mm in thickness).
  • the sensitivity characteristics obtained are entirely compatible with the pressure variations to be measured which are of the order of a few millimeters of mercury.
  • membranes with a precise perforation allowing water, ions, lactates, but not glucose to pass through. Such membranes are said to be hemipermeable to glucose.
  • the diameter of the perforations is, in this case, between approximately between 0.6nm and 0.74nm.
  • Biocompatible coatings are also known which are permeable to glucose and to many molecules, but impermeable to cells.
  • Such coatings such as the perfluoro-sulfonic acid polymer (Nafion ⁇ by Du Pont de Nemours) have the advantage of not becoming blocked after several years in interstitial territory and of not being rejected by the body.
  • Such a coating can therefore advantageously be used as a biocompatible protective membrane.
  • the device according to the invention makes it possible to measure an absolute osmotic pressure, or differences in osmotic pressure, relative to the molecules of a bulk equivalent to that of glucose precisely.
  • an electronic system By coupling the two pressure sensors to an electronic system, the measured values can be communicated to a receiver located outside the individual.
  • Such an electronic system can be, in particular, a passive system of resonant type LC at variable frequency, responding to a Radio Frequency signal emitted from the outside. In this case, the electronic system does not require an energy source and can therefore remain installed for the very long term.
  • FIG. 1 shows the different elements constituting one of the two measurement chambers constituting the device according to the invention, located in an environment 1 for which it is desired to measure the osmotic pressure due to molecules of bulk equivalent to that of glucose.
  • the two measurement chambers being equivalent from the point of view of their operation, we will content our with describing the first of them which is distinguished from the second only by the properties of the hemipemable membrane used.
  • FIG. 1 shows the two parts A and B constituting an exploded view of this measurement chamber according to a sagittal section plane passing through its middle.
  • the membrane 20 is hemipermeable to glucose in nature, that is to say permeable to water and to molecules smaller than glucose, but impermeable to glucose.
  • the thickness of this membrane will be chosen according to its nature.
  • the cavity 41 machined by photolithographic process (with chemical attack with KOH) in a silicon layer 40 of approximately 30 »m thickness, represents the internal chamber for measuring the osmotic pressure.
  • the pressure sensor consists of the membrane 10 and of the layer 12 as well as of the cavity 11, the membrane 10 being directly related to the internal measurement chamber 41.
  • the membrane 10 is a p + doped silicon membrane of approximately 20 ”m thick, oxidized on the peripheral region 53, on the one hand, and 52, on the other hand, so as to be welded by hot process (bonding process) at 1000 ° C. to layer 12, respectively 40.
  • the layer 53 also serves as an insulator between the membrane 10 and the layer 12 so as to constitute a variable capacitor.
  • the layer 12, about 60 "m thick, is hollowed out at its center, by photolithographic process (with chemical attack with KOH), so as to form a cavity 11 about 20" m thick opposite the layer 10.
  • This cavity 11 must be perfectly sealed to ensure good precision and a low drift of the pressure sensor over time.
  • the pressure sensor therefore functions as a variable capacitor, the capacity of which varies as a function of the deformations of the membrane 10, under the effect of the pressure prevailing in the chamber 41.
  • the membrane 20 is stiffened by a layer 30 made, for example, of silicon according to the technique described by Gjermund Kittilsland and Göran Stemme (Depart. of Solid State Electronics, Chalmer Univ. of Technology, Gothenburg, Sweden) and presented in Montreux, Switzerland, at the "Transducer 89" congress, June 26, 1989.
  • a layer 30 made, for example, of silicon according to the technique described by Gjermund Kittilsland and Göran Stemme (Depart. of Solid State Electronics, Chalmer Univ. of Technology, Gothenburg, Sweden) and presented in Montreux, Switzerland, at the "Transducer 89" congress, June 26, 1989.
  • a layer 30 made, for example, of silicon according to the technique described by Gjermund Kittilsland and Göran Stemme (Depart. of Solid State Electronics, Chalmer Univ. of Technology, Gothenburg, Sweden) and presented in Montreux, Switzerland, at the "Transducer 89" congress, June 26, 1989.
  • Such a layer
  • This type of layer is obtained by welding 2 perforated silicon membranes 31 and 32, the perforations not overlapping and the welding being obtained hot (bonding process) thanks to a thin layer of silicon oxide 33 on the two surfaces. opposite and whose thickness is perfectly known.
  • This layer 30 is oxidized at the periphery 51, on the opposite face of the layer 40, so that it can be welded to it hot (bonding process).
  • a layer of the same kind, 35 (consisting of perforated membranes 36 and 37, as well as a thin layer of silicon oxide 38), can also be placed on the other side of the membrane 20.
  • a biocompatible protective layer 60 covers the entire device.
  • a layer must, in particular, be permeable to molecules smaller than glucose, as well as to glucose. It may, for example, be a layer of perfluorosulfonic acid polymer whose long-term resistance is excellent in subcutaneous tissue. The protection provided by this layer relates in particular to cells and deposits such as fibrin.
  • the second measurement chamber constituting the device is identical to the first measurement chamber thus described with the only difference of its membrane 20 which is chosen permeable limit to glucose, that is to say that it lets pass the glucose but not the molecules bigger than glucose.
  • the size of such a device is entirely compatible with its location since its thickness can be around 300 "m and its sides around 2mm.
  • FIG. 2 shows the electronic operation for each of the measurement chambers of the device, based on the principle of a passive resonant circuit of the LC type.
  • the capacitor C is obtained by the pressure sensor constituted by the layers 10 and 12, isolated from each other by the layer of silicon oxide 53. Any movement of the membrane 10, under the effect of pressure variations in the chamber 41, causes a change in the value of C.
  • This resonant frequency is measured remotely by a magnetically coupled oscillator which converts the value measured into osmotic pressure in the cavity 41 and, by difference between the two values obtained at the level of the two measurement chambers, into osmotic pressure due to the molecules of which I he congestion is identical to that of glucose and, by deduction and reference to a basic value, in glucose level.
  • This external electronic assembly therefore includes, for each of the two measurement chambers, an assembly consisting of a variable frequency oscillator 5, a choke L 'and a resonance detector 6 at the terminals of a resistor 7, the resonance characteristics for each of these measurement chambers being different so that they can be analyzed from the outside without interference.
  • a concentration of macro-molecules In order to be in the optimal measurement conditions, a function of physiological variations and of the characteristics of the pressure sensor, it is possible to define a concentration of macro-molecules to be placed inside the osmotic pressure measurement cavity 41.
  • several individual measurement chambers can be used in parallel to simulate a single measurement chamber of the device, each of these multiple individual measurement chambers having in its internal measurement chamber a different concentration of macro molecules.
  • the resonant frequencies of each of the sensors will be chosen to be different, so that each of the individual measurement sensors can be analyzed from the outside without creating interference.
  • FIG. 3 represents a type of resonant frequency curve which can be obtained from the pressure sensor described above. It can be seen that the maximum sensitivity is obtained for a certain range P of pressure variation which should be adapted to the useful range G for measuring the glucose level in the diabetic.
  • a particular location of the implant may be chosen.
  • the peritoneal cavity, the interstitial subcutaneous tissue are, from this point of view, more favorable regions.
  • the abdominal subcutaneous region for example, may be particularly indicated given the ease and safety of the implantation of the device in this location.
  • the two measurement chambers described to form the device can advantageously be produced in the same housing, or even result from photolithography operations on the same substrate.
  • Another advantage of the invention is to be able to couple the information obtained by the measurement device directly to an insulin micro-pump, so as to allow automatic adjustment of the doses of insulin to be administered to the patient.
  • Such a global system allowing to constitute a true artificial pancreas.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Medical Informatics (AREA)
  • Surgery (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Emergency Medicine (AREA)
  • Molecular Biology (AREA)
  • Optics & Photonics (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
  • Investigating Or Analysing Biological Materials (AREA)
  • Measuring And Recording Apparatus For Diagnosis (AREA)
EP90914732A 1989-10-06 1990-10-05 Dispositif implantable d'evaluation du taux de glucose Expired - Lifetime EP0451233B1 (fr)

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
FR8913069A FR2652736A1 (fr) 1989-10-06 1989-10-06 Dispositif implantable d'evaluation du taux de glucose.
FR8913069 1989-10-06
PCT/EP1990/001678 WO1991004704A1 (fr) 1989-10-06 1990-10-05 Dispositif implantable d'evaluation du taux de glucose

Publications (2)

Publication Number Publication Date
EP0451233A1 EP0451233A1 (fr) 1991-10-16
EP0451233B1 true EP0451233B1 (fr) 1995-03-01

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Family Applications (1)

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EP90914732A Expired - Lifetime EP0451233B1 (fr) 1989-10-06 1990-10-05 Dispositif implantable d'evaluation du taux de glucose

Country Status (11)

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US (1) US5337747A (da)
EP (1) EP0451233B1 (da)
JP (1) JP2784259B2 (da)
AT (1) ATE119006T1 (da)
AU (1) AU638067B2 (da)
CA (1) CA2044150C (da)
DE (1) DE69017428T2 (da)
DK (1) DK0451233T3 (da)
ES (1) ES2071115T3 (da)
FR (1) FR2652736A1 (da)
WO (1) WO1991004704A1 (da)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2024039711A1 (en) * 2022-08-16 2024-02-22 The United States Government As Represented By The Department Of Veterans Affairs Pressure sensor apparatus and systems and methods comprising same

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JP2784259B2 (ja) 1998-08-06
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FR2652736A1 (fr) 1991-04-12
DE69017428T2 (de) 1995-09-21
AU638067B2 (en) 1993-06-17
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ATE119006T1 (de) 1995-03-15
US5337747A (en) 1994-08-16
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CA2044150A1 (fr) 1991-04-07
AU6510090A (en) 1991-04-28

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